Method and system for providing calibration of an analyte sensor in an analyte monitoring system

ABSTRACT

Method and apparatus for providing calibration of analyte sensor including applying a control signal, detecting a measured response to the control signal, determining a variance in the detected measured response, and estimating a sensor sensitivity based on the variance in the detected measured response is provided.

RELATED APPLICATIONS

The present application is a continuation of U.S. patent applicationSer. No. 13/766,673 filed Feb. 13, 2013, which is a continuation of U.S.patent application Ser. No. 12/624,377 filed Nov. 23, 2009, now U.S.Pat. No. 8,376,945, which is a continuation of U.S. patent applicationSer. No. 11/463,582 filed Aug. 9, 2006, now U.S. Pat. No. 7,653,425,entitled “Method and System for Providing Calibration of an AnalyteSensor in an Analyte Monitoring System”, the disclosures of each ofwhich are incorporated herein by reference for all purposes.

BACKGROUND

Analyte, e.g., glucose monitoring systems including continuous anddiscrete monitoring systems generally include a small, lightweightbattery powered and microprocessor controlled system which is configuredto detect signals proportional to the corresponding measured glucoselevels using an electrometer, and RF signals to transmit the collecteddata. One aspect of certain analyte monitoring systems include atranscutaneous or subcutaneous analyte sensor configuration which is,for example, partially mounted on the skin of a subject whose analytelevel is to be monitored. The sensor cell may use a two orthree-electrode (work, reference and counter electrodes) configurationdriven by a controlled potential (potentiostat) analog circuit connectedthrough a contact system.

To obtain accurate data from the analyte sensor, calibration isnecessary. Typically, blood glucose measurements are periodicallyobtained using, for example, a blood glucose meter, and the measuredblood glucose values are used to calibrate the sensors. Indeed, thepatient must calibrate each new analyte sensor using for example,capillary blood glucose measurements. This may be inconvenient for thepatient.

In view of the foregoing, it would be desirable to have a method andsystem for calibrating analyte sensors of an analyte monitoring systemthat does not inconveniently require periodic blood glucose measurementsfor sensor calibration.

SUMMARY OF THE INVENTION

In view of the foregoing, in accordance with the various embodiments ofthe present invention, there is provided a method and system forproviding substantially automatic and substantially real timecalibration of analyte sensors for use in an analyte monitoring system.

These and other objects, features and advantages of the presentinvention will become more fully apparent from the following detaileddescription of the embodiments, the appended claims and the accompanyingdrawings.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 illustrates a block diagram of a data monitoring and managementsystem for practicing one embodiment of the present invention;

FIG. 2 is a block diagram of the transmitter unit of the data monitoringand management system shown in FIG. 1 in accordance with one embodimentof the present invention;

FIG. 3 is a block diagram of the receiver/monitor unit of the datamonitoring and management system shown in FIG. 1 in accordance with oneembodiment of the present invention;

FIG. 4 is a flowchart illustrating the analyte sensor sensitivityestimation procedure in accordance with one embodiment of the presentinvention;

FIG. 5 is a flowchart illustrating the analyte sensor parameterestimation procedure in accordance with one embodiment of the presentinvention;

FIG. 6 is a flowchart illustrating an analyte sensor sensitivityestimation procedure in accordance with another embodiment of thepresent invention;

FIG. 7A illustrates the transmission of the control signal from thetransmitter processor in accordance with one embodiment of the presentinvention;

FIG. 7B illustrates the measured response to the control signal from thetransmitter processor shown in FIG. 7A in accordance with one embodimentof the present invention;

FIG. 8 is a tabular illustration of a lookup table for sensorsensitivity for use with the calibration procedure in accordance withone embodiment of the present invention; and

FIG. 9 is a flowchart illustrating the analyte sensor sensitivityestimation procedure in accordance with another embodiment of thepresent invention.

DETAILED DESCRIPTION

As described in detail below, in accordance with the various embodimentsof the present invention, there is provided a method and system fordetermining sensor sensitivity of an analyte sensor which may be used tocalibrate the analyte sensor in the analyte monitoring system. Inparticular, within the scope of the present invention, there is providedmethod and system for automatically calibrating subcutaneous ortranscutaneously positioned analyte sensors such that the frequency ofcapillary blood glucose measurement for calibration of the sensors maybe minimized.

More specifically, FIG. 1 illustrates a data monitoring and managementsystem such as, for example, analyte (e.g., glucose) monitoring system100 in accordance with one embodiment of the present invention. Thesubject invention is further described primarily with respect to aglucose monitoring system for convenience and such description is in noway intended to limit the scope of the invention. It is to be understoodthat the analyte monitoring system may be configured to monitor avariety of analytes, e.g., lactate, and the like.

Analytes that may be monitored include, for example, acetyl choline,amylase, bilirubin, cholesterol, chorionic gonadotropin, creatine kinase(e.g., CK-MB), creatine, DNA, fructosamine, glucose, glutamine, growthhormones, hormones, ketones, lactate, peroxide, prostate-specificantigen, prothrombin, RNA, thyroid stimulating hormone, and troponin.The concentration of drugs, such as, for example, antibiotics (e.g.,gentamicin, vancomycin, and the like), digitoxin, digoxin, drugs ofabuse, theophylline, and warfarin, may also be monitored.

The analyte monitoring system 100 includes a sensor 101, a transmitterunit 102 coupled to the sensor 101, and a receiver unit 104 which isconfigured to communicate with the transmitter unit 102 via acommunication link 103. The receiver unit 104 may be further configuredto transmit data to a data processing terminal 105 for evaluating thedata received by the receiver unit 104. Moreover, the data processingterminal in one embodiment may be configured to receive data directlyfrom the transmitter unit 102 via a communication link 106 which mayoptionally be configured for bi-directional communication.

Only one sensor 101, transmitter unit 102, receiver unit 104,communication link 103, and data processing terminal 105 are shown inthe embodiment of the analyte monitoring system 100 illustrated inFIG. 1. However, it will be appreciated by one of ordinary skill in theart that the analyte monitoring system 100 may include one or moresensor 101, transmitter unit 102, receiver unit 104, communication link103, and data processing terminal 105. Moreover, within the scope of thepresent invention, the analyte monitoring system 100 may be a continuousmonitoring system, or semi-continuous, or a discrete monitoring system.In a multi-component environment, each device is configured to beuniquely identified by each of the other devices in the system so thatcommunication conflict is readily resolved between the variouscomponents within the analyte monitoring system 100.

In one embodiment of the present invention, the sensor 101 is physicallypositioned in or on the body of a user whose analyte level is beingmonitored. The sensor 101 may be configured to continuously sample theanalyte level of the user and convert the sampled analyte level into acorresponding data signal for transmission by the transmitter unit 102.In one embodiment, the transmitter unit 102 is mounted on the sensor 101so that both devices are positioned on the user's body. The transmitterunit 102 performs data processing such as filtering and encoding on datasignals, each of which corresponds to a sampled analyte level of theuser, for transmission to the receiver unit 104 via the communicationlink 103.

In one embodiment, the analyte monitoring system 100 is configured as aone-way RF communication path from the transmitter unit 102 to thereceiver unit 104. In such embodiment, the transmitter unit 102transmits the sampled data signals received from the sensor 101 withoutacknowledgement from the receiver unit 104 that the transmitted sampleddata signals have been received. For example, the transmitter unit 102may be configured to transmit the encoded sampled data signals at afixed rate (e.g., at one minute intervals) after the completion of theinitial power on procedure. Likewise, the receiver unit 104 may beconfigured to detect such transmitted encoded sampled data signals atpredetermined time intervals. Alternatively, the analyte monitoringsystem 100 may be configured with a bi-directional RF (or otherwise)communication between the transmitter unit 102 and the receiver unit104.

Additionally, in one aspect, the receiver unit 104 may include twosections. The first section is an analog interface section that isconfigured to communicate with the transmitter unit 102 via thecommunication link 103. In one embodiment, the analog interface sectionmay include an RF receiver and an antenna for receiving and amplifyingthe data signals from the transmitter unit 102, which are thereafter,demodulated with a local oscillator and filtered through a band-passfilter. The second section of the receiver unit 104 is a data processingsection which is configured to process the data signals received fromthe transmitter unit 102 such as by performing data decoding, errordetection and correction, data clock generation, and data bit recovery.

In operation, upon completing the power-on procedure, the receiver unit104 is configured to detect the presence of the transmitter unit 102within its range based on, for example, the strength of the detecteddata signals received from the transmitter unit 102 or a predeterminedtransmitter identification information. Upon successful synchronizationwith the corresponding transmitter unit 102, the receiver unit 104 isconfigured to begin receiving from the transmitter unit 102 data signalscorresponding to the user's detected analyte level. More specifically,the receiver unit 104 in one embodiment is configured to performsynchronized time hopping with the corresponding synchronizedtransmitter unit 102 via the communication link 103 to obtain the user'sdetected analyte level.

Referring again to FIG. 1, the data processing terminal 105 may includea personal computer, a portable computer such as a laptop or a handhelddevice (e.g., personal digital assistants (PDAs)), and the like, each ofwhich may be configured for data communication with the receiver via awired or a wireless connection. Additionally, the data processingterminal 105 may further be connected to a data network (not shown) forstoring, retrieving and updating data corresponding to the detectedanalyte level of the user.

Within the scope of the present invention, the data processing terminal105 may include an infusion device such as an insulin infusion pump orthe like, which may be configured to administer insulin to patients, andwhich may be configured to communicate with the receiver unit 104 forreceiving, among others, the measured analyte level. Alternatively, thereceiver unit 104 may be configured to integrate an infusion devicetherein so that the receiver unit 104 is configured to administerinsulin therapy to patients, for example, for administering andmodifying basal profiles, as well as for determining appropriate bolusesfor administration based on, among others, the detected analyte levelsreceived from the transmitter unit 102.

Additionally, the transmitter unit 102, the receiver unit 104 and thedata processing terminal 105 may each be configured for bi-directionalwireless communication such that each of the transmitter unit 102, thereceiver unit 104 and the data processing terminal 105 may be configuredto communicate (that is, transmit data to and receive data from) witheach other via the wireless communication link 103. More specifically,the data processing terminal 105 may in one embodiment be configured toreceive data directly from the transmitter unit 102 via thecommunication link 106, where the communication link 106, as describedabove, may be configured for bi-directional communication.

In this embodiment, the data processing terminal 105 which may includean insulin pump, may be configured to receive the analyte signals fromthe transmitter unit 102, and thus, incorporate the functions of thereceiver unit 104 including data processing for managing the patient'sinsulin therapy and analyte monitoring. In one embodiment, thecommunication link 103 may include one or more of an RF communicationprotocol, an infrared communication protocol, a Bluetooth® enabledcommunication protocol, an 802.11x wireless communication protocol, oran equivalent wireless communication protocol which would allow secure,wireless communication of several units (for example, per HIPAArequirements) while avoiding potential data collision and interference.

FIG. 2 is a block diagram of the transmitter unit of the data monitoringand detection system shown in FIG. 1 in accordance with one embodimentof the present invention. Referring to the Figure, the transmitter unit102 in one embodiment includes an analog interface 201 configured tocommunicate with the sensor 101 (FIG. 1), a user input 202, and atemperature detection section 203, each of which is operatively coupledto a transmitter processor 204 such as a central processing unit (CPU).There are provided four contacts (not shown), three of which areelectrodes—work electrode, guard contact, reference electrode, andcounter electrode, each operatively coupled to the analog interface 201of the transmitter unit 102 for connection to the sensor 101 (FIG. 1).In one embodiment, each of the work electrode, guard contact, referenceelectrode, and counter electrode may be made using a conductive materialthat is either printed or etched, for example, such as carbon which maybe printed, or metal foil (e.g., gold) which may be etched.

Further shown in FIG. 2 are a transmitter serial communication section205 and an RF transmitter 206, each of which is also operatively coupledto the transmitter processor 204. Moreover, a power supply 207 such as abattery is also provided in the transmitter unit 102 to provide thenecessary power for the transmitter unit 102. Additionally, as can beseen from the Figure, clock 208 is provided to, among others, supplyreal time information to the transmitter processor 204.

In one embodiment, a unidirectional input path is established from thesensor 101 (FIG. 1) and/or manufacturing and testing equipment to theanalog interface 201 of the transmitter unit 102, while a unidirectionaloutput is established from the output of the RF transmitter 206 of thetransmitter unit 102 for transmission to the receiver unit 104. In thismanner, a data path is shown in FIG. 2 between the aforementionedunidirectional input and output via a dedicated link 209 from the analoginterface 201 to serial communication section 205, thereafter to theprocessor 204, and then to the RF transmitter 206. As such, in oneembodiment, via the data path described above, the transmitter unit 102is configured to transmit to the receiver unit 104 (FIG. 1), via thecommunication link 103 (FIG. 1), processed and encoded data signalsreceived from the sensor 101 (FIG. 1). Additionally, the unidirectionalcommunication data path between the analog interface 201 and the RFtransmitter 206 discussed above allows for the configuration of thetransmitter unit 102 for operation upon completion of the manufacturingprocess as well as for direct communication for diagnostic and testingpurposes.

As discussed above, the transmitter processor 204 is configured totransmit control signals to the various sections of the transmitter unit102 during the operation of the transmitter unit 102. In one embodiment,the transmitter processor 204 also includes a memory (not shown) forstoring data such as the identification information for the transmitterunit 102, as well as the data signals received from the sensor 101. Thestored information may be retrieved and processed for transmission tothe receiver unit 104 under the control of the transmitter processor204. Furthermore, the power supply 207 may include a commerciallyavailable battery.

The transmitter unit 102 is also configured such that the power supplysection 207 is capable of providing power to the transmitter for aminimum of about three months of continuous operation after having beenstored for about eighteen months in a low-power (non-operating) mode. Inone embodiment, this may be achieved by the transmitter processor 204operating in low power modes in the non-operating state, for example,drawing no more than approximately 1 μA of current. Indeed, in oneembodiment, the final step during the manufacturing process of thetransmitter unit 102 may place the transmitter unit 102 in the lowerpower, non-operating state (i.e., post-manufacture sleep mode). In thismanner, the shelf life of the transmitter unit 102 may be significantlyimproved.

Moreover, as shown in FIG. 2, while the power supply unit 207 is shownas coupled to the processor 204, and as such, the processor 204 isconfigured to provide control of the power supply unit 207, it should benoted that within the scope of the present invention, the power supplyunit 207 is configured to provide the necessary power to each of thecomponents of the transmitter unit 102 shown in FIG. 2.

Referring back to FIG. 2, the power supply section 207 of thetransmitter unit 102 in one embodiment may include a rechargeablebattery unit that may be recharged by a separate power supply rechargingunit (for example, provided in the receiver unit 104) so that thetransmitter unit 102 may be powered for a longer period of usage time.Moreover, in one embodiment, the transmitter unit 102 may be configuredwithout a battery in the power supply section 207, in which case thetransmitter unit 102 may be configured to receive power from an externalpower supply source (for example, a battery) as discussed in furtherdetail below.

Referring yet again to FIG. 2, the temperature detection section 203 ofthe transmitter unit 102 is configured to monitor the temperature of theskin near the sensor insertion site. The temperature reading is used toadjust the analyte readings obtained from the analog interface 201. TheRF transmitter 206 of the transmitter unit 102 may be configured foroperation in the frequency band of 315 MHz to 322 MHz, for example, inthe United States. Further, in one embodiment, the RF transmitter 206 isconfigured to modulate the carrier frequency by performing FrequencyShift Keying and Manchester encoding. In one embodiment, the datatransmission rate is 19,200 symbols per second, with a minimumtransmission range for communication with the receiver unit 104.

Additional detailed description of the continuous analyte monitoringsystem, its various components including the functional descriptions ofthe transmitter are provided in U.S. Pat. No. 6,175,752 issued Jan. 16,2001 entitled “Analyte Monitoring Device and Methods of Use”, and inU.S. patent application Ser. No. 10/745,878 filed Dec. 26, 2003, nowU.S. Pat. No. 7,811,231, entitled “Continuous Glucose Monitoring Systemand Methods of Use”, each assigned to the Assignee of the presentapplication.

FIG. 3 is a block diagram of the receiver/monitor unit of the datamonitoring and management system shown in FIG. 1 in accordance with oneembodiment of the present invention. Referring to FIG. 3, the receiverunit 104 includes a blood glucose test strip interface 301, an RFreceiver 302, an input 303, a temperature detection section 304, and aclock 305, each of which is operatively coupled to a receiver processor307. As can be further seen from the Figure, the receiver unit 104 alsoincludes a power supply 306 operatively coupled to a power conversionand monitoring section 308. Further, the power conversion and monitoringsection 308 is also coupled to the receiver processor 307. Moreover,also shown are a receiver serial communication section 309, and anoutput 310, each operatively coupled to the receiver processor 307.

In one embodiment, the test strip interface 301 includes a glucose leveltesting portion to receive a manual insertion of a glucose test strip,and thereby determine and display the glucose level of the test strip onthe output 310 of the receiver unit 104. This manual testing of glucosecan be used to calibrate sensor 101. The RF receiver 302 is configuredto communicate, via the communication link 103 (FIG. 1) with the RFtransmitter 206 of the transmitter unit 102, to receive encoded datasignals from the transmitter unit 102 for, among others, signal mixing,demodulation, and other data processing. The input 303 of the receiverunit 104 is configured to allow the user to enter information into thereceiver unit 104 as needed. In one aspect, the input 303 may includeone or more keys of a keypad, a touch-sensitive screen, or avoice-activated input command unit. The temperature detection section304 is configured to provide temperature information of the receiverunit 104 to the receiver processor 307, while the clock 305 provides,among others, real time information to the receiver processor 307.

Each of the various components of the receiver unit 104 shown in FIG. 3is powered by the power supply 306 which, in one embodiment, includes abattery. Furthermore, the power conversion and monitoring section 308 isconfigured to monitor the power usage by the various components in thereceiver unit 104 for effective power management and to alert the user,for example, in the event of power usage which renders the receiver unit104 in sub-optimal operating conditions. An example of such sub-optimaloperating condition may include, for example, operating the vibrationoutput mode (as discussed below) for a period of time thus substantiallydraining the power supply 306 while the processor 307 (thus, thereceiver unit 104) is turned on. Moreover, the power conversion andmonitoring section 308 may additionally be configured to include areverse polarity protection circuit such as a field effect transistor(FET) configured as a battery activated switch.

The serial communication section 309 in the receiver unit 104 isconfigured to provide a bi-directional communication path from thetesting and/or manufacturing equipment for, among others,initialization, testing, and configuration of the receiver unit 104.Serial communication section 104 can also be used to upload data to acomputer, such as time-stamped blood glucose data. The communicationlink with an external device (not shown) can be made, for example, bycable, infrared (IR) or RF link. The output 310 of the receiver unit 104is configured to provide, among others, a graphical user interface (GUI)such as a liquid crystal display (LCD) for displaying information.Additionally, the output 310 may also include an integrated speaker foroutputting audible signals as well as to provide vibration output ascommonly found in handheld electronic devices, such as mobile telephonespresently available. In a further embodiment, the receiver unit 104 alsoincludes an electro-luminescent lamp configured to provide backlightingto the output 310 for output visual display in dark ambientsurroundings.

Referring back to FIG. 3, the receiver unit 104 in one embodiment mayalso include a storage section such as a programmable, non-volatilememory device as part of the processor 307, or provided separately inthe receiver unit 104, operatively coupled to the processor 307. Theprocessor 307 is further configured to perform Manchester decoding aswell as error detection and correction upon the encoded data signalsreceived from the transmitter unit 102 via the communication link 103.

Referring back to the Figures, as described in further detail below, inone embodiment of the present invention, the transmitter processor 204may be configured to transmit a control signal to the analog interface201 to determine the poise voltage between the work electrode and thereference electrode of the sensor 101, each of which are operativelycoupled to the analog interface 201 of the transmitter unit 102.

More specifically, in one embodiment, a control processor component ofthe transmitter unit 102 processor 204 is configured to provide aperturbation control signal to the analog interface 201. The analoginterface 201 is configured to translate the received perturbationcontrol signal to a perturbation that affects the sensor response. Forexample, the control signal in one embodiment may be configured tocontrol the voltage level that is applied to the sensor 101 between thework and reference electrodes (i.e., the poise voltage). In oneembodiment, the analog interface 201 of the transmitter unit 102 isconfigured to translate the sensor response to the perturbation to acorresponding response signal that is acquired by the signal processingcomponent of the processor 204 of the transmitter unit 102. The signalprocessing component of the processor 204 in the transmitter unit 102 inone embodiment may be configured to determine the desired sensorparameter estimation which is transmitted to the receiver unit 104.Alternatively, the signal processing component of the processor 204 inthe transmitter unit 102 may be configured to preprocess the data, whichare then transmitted to the receiver unit for sensor parameterestimation determination.

More specifically, FIG. 4 is a flowchart illustrating analyte sensorsensitivity estimation procedure in accordance with one embodiment ofthe present invention. Referring to FIG. 4, at step 410, the transmitterprocessor 204 (FIG. 2) in one embodiment is configured to provide acontrol signal to the analog interface 201 (for example a poise voltagecontrol circuit) of the transmitter unit 102. In one aspect, the controlsignal provides a perturbation input to determine the poise voltagebetween the work electrode and the reference electrode of the sensor101. In one aspect, the poise voltage may be in the range ofapproximately −600 mV and 600 mV, and the analog interface 201 may beconfigured to control the poise voltage and apply the poise voltage tothe electrodes of the sensor 101.

One embodiment of the control signal perturbations is shown in FIG. 7Awhich illustrates the control signal from the transmitter processor 204so as to provide a poise voltage waveform that is a square wave of 50%duty cycle with a one minute time period interval. In one embodiment,the poise voltage square wave amplitude may be switched from 40 mV to−600 mV from, for example, the normal operating poise voltage to apredetermined level such as −600 mV which effectively shuts down thecurrent signal on the work electrode.

Referring back to FIG. 4, at step 420, the analog interface 201 in oneembodiment is configured to determine a measured response to thereceived control signal, for example, a voltage signal which issubstantially proportional to the current signal level on the workelectrode of the sensor 101. An aspect of the measured response isillustrated in FIG. 7B. As shown, in one aspect, the current signallevel is associated with the analyte level of the patient and may bemodulated by the poise voltage perturbations driven by the controlsignal from the transmitter processor 204. Thereafter at step 430, thetransmitter processor 204 may be optionally configured to synchronizethe measured response from the analog interface 201 with the controlsignal. The transmitter processor 204 may be further configured to storethe measured response and the associated control signal in a storageunit (not shown) such as a memory device.

Referring again to FIG. 4, the transmitter processor 204 in oneembodiment is configured to determine the difference or variance in themeasured response based on the control signal 440, and the sensorsensitivity may be determined based on the determined difference inmeasured response 450. That is, in one embodiment, the difference inmeasured response is compared to a look up table stored, for example, inthe transmitter processor 204 memory unit which includes calculatedmeasured response difference for the sensor based on characteristics ofthe sensor 101.

By way of an example, for a measured response difference of 47 analog todigital counts, the lookup table for sensor sensitivity (FIG. 8)indicates 34.5 pA/(mg/dL) for the sensor. Then, the determined sensorsensitivity may be applied to the work electrode current to determinethe corresponding calibrated analyte value. That is, the calibratedanalyte value may be determined by dividing the work electrode currentsignal by the sensor sensitivity.

FIG. 5 is a flowchart illustrating the analyte sensor parameterestimation procedure in accordance with one embodiment of the presentinvention. Referring to FIG. 5, at step 510, a perturbation controlsignal is applied to the sensor 101 (FIG. 1), and then the response tothe perturbation control signal is measured at step 520. Based on themeasured response to the perturbation control signal, at step 530, thesensor parameter(s) is estimated and at step 540, the analyte level isestimated based on the measured response to the perturbation controlsignal. In one embodiment, the procedure shown in FIG. 5 is repeatedcontinuously.

In accordance with the various embodiments of the present invention,different estimates may be determined including, for example, estimationof sensor properties such as sensitivity and response time, the analytelevel, and analyte level validity/accuracy. In one embodiment, there areseveral mechanisms that may be used to perturb the sensor 101 (FIG. 1),for example, the variable poise voltage. In a further aspect, the one ormore of the perturbation control signals may include, for example,square waves. Also, in one aspect, the one or more physical sensorresponses that are measured may include, for example, work electrodecurrent variation due to poise voltage perturbation. In addition, signalprocessing may be used in one embodiment to estimate the sensorparameter or analyte level from the sensor response to the perturbationas described above.

FIG. 6 is a flowchart illustrating an analyte sensor sensitivityestimation procedure in accordance with another embodiment of thepresent invention. Referring to FIG. 6, a control signal is applied 610,for example, to the analog interface 201 of the transmitter unit 102(FIG. 1). That is, in one embodiment, the processor 204 of thetransmitter unit 102 may be configured to provide a control signal to apoise voltage control circuit (for example, incorporated in theprocessor 204 of the transmitter unit 102 as shown in FIG. 2, but whichmay, in one embodiment, be separately provided within the transmitterunit 102) of the transmitter unit 102.

In one aspect, the control signal may be configured to provide aperturbation input signal to determine the poise voltage between thework electrode and the reference electrode of the sensor 101. In oneembodiment, the poise voltage may be in the range of approximately −600mV and 600 mV, and the analog interface 201 may be configured to controlthe poise voltage and apply the poise voltage to the electrodes of thesensor 101.

As described in further detail below, an embodiment of the controlsignal perturbations is shown in FIG. 7A which illustrates the controlsignal from the processor 204 (FIG. 2) to provide a poise voltagewaveform that is a square wave of 50% duty cycle with a one minute timeperiod interval. Referring to FIG. 7A, in one embodiment, the poisevoltage square wave amplitude may be switched from 40 mV to −600 mVfrom, for example, the normal operating poise voltage to a predeterminedlevel such as −600 mV which effectively shuts down the current signal onthe work electrode.

Referring back to FIG. 6, the analog interface 201 in one embodiment isconfigured to determine a measured response to the received controlsignal 620, for example, a voltage signal which is substantiallyproportional to the current signal level on the work electrode of thesensor 101 (FIG. 1). As discussed in further detail below, oneembodiment of the measured response is shown in FIG. 7B. Referring toFIG. 7B, in one embodiment, the average signal level for half of theduty cycle is associated with the analyte level of the patient, but thetransient within the half-duty cycle period, caused by the poise voltageperturbations driven by the control signal from the transmitterprocessor 204, is associated with the sensitivity parameter of thesensor 101. The transmitter processor 204 may be further configured tostore the measured response and the associated control signal in astorage unit (not shown) such as a memory device.

Referring again to FIG. 6, the transmitter processor 204 in oneembodiment is configured to determine the amplitude difference of thetransient from the start of the half-duty cycle to the end (referred tosometimes as the “on” period) in the measured response 630, and thesensor sensitivity may be determined based on the determined differencein the response 640. That is, in one embodiment, the difference inmeasured response is compared to a predetermined sensor parameter suchas sensor sensitivity that may be stored in a look up table, forexample, in the transmitter processor 204 memory unit. In one aspect,the look up table may include a calculated measured response differencefor the sensor 101 and corresponding sensor sensitivities based oncharacteristics of the sensor 101.

In one embodiment, the transmitter may be configured to determine thissensitivity value once per minute, and to transmit the sensitivity valueit to the receiver unit 104 (FIG. 1) in addition to data or signalcorresponding to the work current signal level, determined at the end ofthe “on” period, and skin temperature.

In one embodiment, the receiver unit 104 (FIG. 1) may be configured toapply the determined sensor sensitivity to the temperature compensatedwork electrode current signal in order to determine the correspondingcalibrated analyte value or level. That is, the calibrated analyte valuemay be determined by dividing the temperature compensated work electrodecurrent signal by the determined sensor sensitivity. In one aspect, atime-series of the calibrated analyte values may be acquired by thereceiver unit 104 (FIG. 1) in real-time, and may be used to determineanalyte rate-of-change and other analyte signal metrics and/orstatistics. In addition, the calibrated analyte values may also be usedto drive alarms or alerts that inform the patient whose analyte is beingmonitored of analyte level conditions that require attention. Inaddition, in accordance with one aspect of the present invention, thereceiver unit 104 may be configured to determine whether the sensorsensitivity range is within a valid range.

FIG. 7A illustrates the transmission of the control signal from thetransmitter processor in accordance with one embodiment of the presentinvention. More particularly, FIG. 7A illustrates the poise voltagesquare wave with 50% duty cycle with one minute time periods is shown,where the poise voltage square wave amplitude is switched from 40 mV to−600 mV as in normal operating mode. FIG. 7B illustrates the measuredresponse to the control signal from the transmitter processor shown inFIG. 7A in accordance with one embodiment of the present invention. Morespecifically, the measured response which is associated with the analytelevel measured by the sensor 101 from the interstitial fluid of apatient as modulated by the control signal from the transmitterprocessor 204 is illustrated with one minute time periods.

FIG. 8 is a tabular illustration of a lookup table for sensorsensitivity for use with the calibration procedure in accordance withone embodiment of the present invention. More specifically, in oneembodiment, the lookup table shown in FIG. 8 is stored in a memory unit(not shown) of the transmitter unit 102 (or alternatively, in thetransmitter processor 204) and may be accessed by the transmitterprocessor 204 to retrieve a corresponding sensitivity value associatedwith the determined measured response difference.

FIG. 9 is a flowchart illustrating the analyte sensor sensitivityestimation procedure in accordance with another embodiment of thepresent invention. Referring to FIG. 9, in one embodiment, a controlsignal from the transmitter processor 204 (FIG. 2) is provided 910 tothe analog interface 201 of the transmitter unit 102, and a response tothe applied control signal is determined 920. Thereafter, the differenceor variance in the determined response to the control signal between thebeginning and end of the half duty cycle is determined 930. As can beseen, in one embodiment, steps 910 to 930 are substantially similar tosteps 610 to 630, respectively described above.

Referring back to FIG. 9, after determining the measured responsevariance or difference between the beginning and end of the half dutycycle, it is determined whether the number of transmitted or appliedcontrol signals exceed a predetermined number or count 940. If it isdetermined that the number of transmitted or applied control signals donot exceed the predetermined number or count, then a control signalcounter (for example, provided in the transmitter unit 102) isincremented by one count 960, and the routine returns to the beginningwhere another control signal is provided to the analog interface 201 ofthe transmitter unit 102.

On the other hand, if it is determined that the number of transmitted orapplied control signals exceeds the predetermined number or count, thenthe sensor sensitivity may be determined based on the determineddifference in the response 950. That is, as discussed above, thedifference in measured response in one embodiment is compared to apredetermined sensor parameter such as sensor sensitivity that may bestored in a look up table, for example, in the transmitter processor 204memory unit. In one aspect, the look up table may include a calculatedmeasured response difference for the sensor and corresponding sensorsensitivities based on characteristics of the sensor. Furthermore, asdiscussed above, in one embodiment, the calibrated analyte value orlevel may be determined by, for example, dividing the correspondingsensor signal (e.g., work electrode current signal) level by thedetermined sensor sensitivity value.

Within the scope of the present invention, the perturbations to theanalyte sensors may be provided by, for example, altering the poisevoltage in time. Alternatively, an additional electrical current signalmay be provided to the sensor work or counter electrodes via an ACcoupling, where the level of the additional electrical current signalmay be varied in time by the control signal in a manner similar asdiscussed above. Still in accordance with another embodiment, thework/counter electrode current path may be opened and closed in a timevarying manner controlled by the control signal. Yet still anotherembodiment may provide a variable resistance in the work/counterelectrode current path, where the variable resistance is varied in timeas controlled by the control signal.

In another aspect of the present invention, the transcutaneouslypositioned sensor may be perturbed with a mechanical transducercontrolled in time and amplitude by a predetermined control signal. Inone embodiment, mechanical transducers may include those that canprovide physical signals of vibration, acoustics, thermal orelectro-magnetic media, for example. Broadly, any suitable mechanism toapply perturbations to the transcutaneously positioned sensor may beused to the extent that the measured response may be analyzed by thesignal processing component such as, for example, the transmitter unitprocessor 204 to estimate one or more sensor properties based on thesignal response induced by the perturbations. For example, vibrationperturbations may induce fluctuations in the sensor membrane that couldbe detected in the measured response transients, which may be correlatedwith membrane thickness and thus provide a measure of the sensitivity ofthe sensor.

In addition, in accordance with the various embodiments of the presentinvention, there are provided a variety of time-varying controls signalsthat may be applied, along with a variety of techniques used to analyzethe measured response and estimate the sensor parameter of interest.Some of these control signals may be appropriate to induce a measuredresponse that is more informative about a specific sensor parameter thanother control signals, and some control signals may be more practical toimplement than others. As discussed previously, a square-wave controlsignal may be employed in one embodiment. Variations in this type ofcontrol signal may be suitably used where the positive and negativeamplitudes are at different levels, the duty cycle is other than 50%, orthe period is other than 1 minute.

In another embodiment of the present invention, a feedback mechanism maybe provided where the duty cycle is varied to achieve a desiredresponse, such as a specific transient response time. In this case, thefinal duty cycle is the parameter that is correlated with the sensorparameter to be estimated. This feedback technique may be extended toother types of control signals, mentioned below, and othercharacteristics of the signal such as phase, amplitude and frequency maybe varied to achieve a desired response.

Alternatively, a sine wave may be used as the control signal discussedabove rather than a square wave. Still alternatively, a series of sinewaves at different frequencies, or a chirp signal may be used as controlsignals in one embodiment of the present invention. The measuredresponse of these perturbation signals may then be analyzed usingstandard spectral analysis techniques. Based on the spectral analysis,metrics may be determined that are correlated with the sensor parameterto be estimated.

In accordance with yet another embodiment, an impulse signal, or aseries of impulse signals may be alternatively used as control signals.The measured response of these perturbation signals may be analyzedusing known impulse response analysis techniques. For example, themaximum height of the measured response may be used to determine theassociated sensor sensitivity. Alternatively, other signal metrics suchas the time to reach the maximum height of the measured response, thearea under the curve of the measured response, the slope of the measuredresponse may be correlated with the sensor parameter to be estimated.

In still another embodiment, pseudo-random modulation similar to thoseused in spread-spectrum communication systems may be used as the controlsignals. The measured response of these perturbation signals may beanalyzed using known spread-spectrum analysis techniques. Based on thisanalysis, metrics may be determined that are correlated with the sensorparameter to be estimated. In addition, the response signal may bedemodulated using spread-spectrum techniques to recover the analytelevel.

For some of the control signal/response measurement analysis techniquesdiscussed above, the relative phase between the control signal and themeasured response may be used to analyze the measured response to theperturbation. For some of the control signal/response measurementanalysis techniques discussed above, multiple metrics may be determined.One or more of these metrics may be used to estimate the sensorparameter of interest. For example, in one embodiment, amultidimensional table lookup may be used where one dimension includesthe sensor parameter of interest, and the other dimensions may each beassociated with a different metric that characterizes the measuredresponse. More specifically, by way of illustration, in the impulseresponse approach described above, both the maximum height and the timeto reach the height of the measured response may be determined. In thiscase, a three dimensional lookup table may be used.

As discussed above, in one embodiment, a lookup table may be used tocorrelate a metric associated with the measured response with a sensorparameter of interest (for example, sensitivity). Alternatively, amathematical function that relates the measured response metric with thesensor parameter may be used. The sensor parameter may then bedetermined based on the measured response metric as an input. In anotheraspect, the estimate of the sensor parameter may be determined for manymeasurements using, for example, the least squares approach.

In addition, within the scope of the present invention, the controlsignal may be transmitted to the analog interface 201 at predeterminedtime periods during the life of the sensor. Alternatively, thetransmitter processor 204 may be configured to transmit the controlsignal only during the time periods when sensor calibration is desiredor if some other factor, such as a detection of sensitivity instability,determines that sensor calibration is required.

Moreover, in one embodiment, other system parameters in addition tosensitivity may be associated with the measured response from the analoginterface 201 in response to the control signal from the transmitterprocessor 204. These include, but are not limited to, sensor responsetime, sensor response linearity, sensitivity stability and sensorfailure. Accurately estimated sensor response time can be useful forincorporation into algorithms that compensate for errors due to lag inthe analyte measurement system. Knowledge of the non-linearity in thesensor response (non-linearity means that the sensitivity is notconstant over the entire range to measured response) allows forcompensation of errors caused by this non-linearity.

Detection of sensitivity instability (that is, detection when thesensitivity has changed value) may be used to accurately determine thenew sensitivity. For example, if instability has been detected by thesignal processing component, it can direct the control processingcomponent such as the transmitter unit processor 204 to initiate acontrol signal that is more appropriate to accurately estimating thesensitivity. Also, detecting a sudden, substantial change in sensitivitymay be used to identify that a sensor may have failed.

While the control signal may be used to determine the sensorsensitivity, in one embodiment, the resulting modulation in the measuredresponse may be removed by, for example, one or more signal filters torecover the glucose signal. In one aspect, a standard signal filter maybe used to remove the high frequency content of the signal due tomodulation by the perturbation control signal, and recover the lowerfrequency content that represents the analyte level. In another aspect,the modulation may be deconvolved using the control signal, thecalculated sensor response and the estimated sensitivity.

Furthermore, there are several approaches to measure a sensor's responseto the perturbation signals in order to estimate desired properties orcharacteristics of the sensor. For example, in one embodiment, theelectrical current that flows through the work (and counter) electrodemay be measured. Alternatively, the perturbation response in the counterelectrode voltage may be alternatively measured. The measured countervoltage response may be analyzed using same or similar techniques as themeasured work current response. In another embodiment, both work currentand counter voltage responses may be measured and analyzed.

In the manner described above, within the scope of the presentinvention, there is provided method and system for performingcalibration of analyte sensors based on the sensor dynamic behavior andon a substantially real time basis such that sensor calibrations basedon blood glucose measurements may be minimized further to improve theaccuracy of the analyte sensor data.

In accordance with the various embodiments of the present invention, thetransmitter processor 204 may include a microcontroller, oralternatively, may be implemented with digital logic such as a gatearray or similar logic devices. In addition, in one embodiment, themeasured response variance as well as the estimated sensor sensitivitydetermined by the transmitter processor 204 may be transmitted to thereceiver unit 104 (FIG. 1) in the analyte monitoring system 100 inaddition to the analyte sensor measurements (for example, the workelectrode current measurements detected by the sensor 101).

In a further aspect, some of the processing may be performed by thereceiver unit 104 (FIG. 1) rather than by the transmitter processor 204such that the transmitter unit 102 may be configured to periodicallytransmit the measured response variance to the receiver unit 104, andthe receiver unit processing and storage unit 307 (FIG. 3) may beconfigured to perform the sensor sensitivity determination based on thelookup table which may be stored in a memory device (not shown) in thereceiver unit 104.

A method of calibrating an analyte sensor in one embodiment includesapplying a control signal, detecting a measured response to the controlsignal, determining a variance in the detected measured response, andestimating a sensor sensitivity based on the variance in the detectedmeasured response.

The level of the control signal may in one embodiment vary in time.

In one aspect, the control signal may include a square wave signal,where the square wave signal may be applied to a poise voltage.

In a further aspect, detecting the measured response may includedetermining a work electrode current signal.

In still another aspect, the variance may be determined based oncomparing the difference between the beginning and end of the half dutycycle of the measured response to the control signal.

Moreover, estimating the sensor sensitivity may include retrieving apredetermined sensor sensitivity corresponding to the determinedvariance in the detected measured response.

The method may also include determining a validity of the estimatedsensor sensitivity.

In addition, the method may also include determining analyte level basedon the estimated sensor sensitivity.

The sensor in one embodiment may include an analyte sensor.

An analyte sensor calibration device in accordance with anotherembodiment includes a processor configured to apply a control signal,detect a measured response to the control signal, determine a variancein the detected measured response, and estimate a sensor sensitivitybased on the variance in the detected measured response.

The processor may be configured to vary the level of the control signalwith time.

In another aspect, the processor may be configured to apply a squarewave signal to a poise voltage.

The processor in a further aspect may be configured to determine a workelectrode current signal of an analyte sensor operatively coupled to theprocessor.

Moreover, the processor may be configured to determine the variancebased on comparing the difference between the beginning and end of thehalf duty cycle of the measured response to the control signal.

In addition, the processor in a further aspect may be configured toretrieve a predetermined sensor sensitivity corresponding to thedetermined variance in the detected measured response.

The processor may be operatively coupled to a data receiver unitconfigured to determine a validity of the estimated sensor sensitivity,where the data receiver unit may be configured to determine an analytelevel based on the estimated sensor sensitivity.

The various processes described above including the processes performedby the transmitter processor 204 in the software application executionenvironment in the transmitter unit 102 including the processes androutines described in conjunction with FIGS. 4-6 and 9, may be embodiedas computer programs developed using an object oriented language thatallows the modeling of complex systems with modular objects to createabstractions that are representative of real world, physical objects andtheir interrelationships. The software required to carry out theinventive process, which may be stored in the memory (not shown) of thetransmitter unit 102 may be developed by a person of ordinary skill inthe art and may include one or more computer program products.

Various other modifications and alterations in the structure and methodof operation of this invention will be apparent to those skilled in theart without departing from the scope and spirit of the invention.Although the invention has been described in connection with specificpreferred embodiments, it should be understood that the invention asclaimed should not be unduly limited to such specific embodiments. It isintended that the following claims define the scope of the presentinvention and that structures and methods within the scope of theseclaims and their equivalents be covered thereby.

What is claimed is:
 1. A method of processing analyte sensor signals,comprising: applying a poise voltage to an analyte sensor; whileapplying the poise voltage to the analyte sensor, applying a controlsignal to the analyte sensor; measuring a response signal based on thepoise voltage and the control signal from the analyte sensor;estimating, with one or more processors, a sensor sensitivity based on apredetermined calculated correlation to a variance in the measuredresponse; and determining a calibrated analyte value based on theestimated sensor sensitivity; wherein the control signal comprises atime-varying perturbation signal that provides for the analyte sensor aduty cycle and the variance is determined from a transient response ofthe analyte sensor to the control signal during the duty cycle.
 2. Themethod of claim 1, wherein measuring the response signal includesdetermining a work electrode current signal.
 3. The method of claim 1,wherein the control signal is a square-wave signal.
 4. The method ofclaim 1, wherein the variance is determined from the difference in themeasured response signal from the analyte sensor between a beginning andan end of an ‘on’ period of the control signal.
 5. The method of claim1, wherein estimating the sensor sensitivity includes retrieving apredetermined sensor sensitivity associated with the determined variancein the measured response.
 6. The method of claim 5, wherein thedetermined variance comprises a number of analog to digital counts. 7.The method of claim 1, further including determining a validity of theestimated sensor sensitivity.
 8. The method of claim 7, whereindetermining the validity of the estimated sensor sensitivity includescomparing the estimated sensor sensitivity to a predetermined range. 9.The method of claim 1, wherein determining the calibrated analyte valueincludes applying the estimated sensor sensitivity to a signal receivedfrom the analyte sensor.
 10. The method of claim 1, wherein thecalibrated analyte value corresponds to an analyte level in bodily fluidunder a skin surface.
 11. A device, comprising: an analyte sensor; aprocessor; and a memory storing instructions which, when executed by theprocessor, cause the processor to: apply a poise voltage to the analytesensor; while applying the poise voltage to the analyte sensor, apply acontrol signal to the analyte sensor; measure a response signal based onthe poise voltage and the control signal from the analyte sensor;estimate, with the processor, a sensor sensitivity based on apredetermined calculated correlation to a variance in the measuredresponse; and determine a calibrated analyte value based on theestimated sensor sensitivity; wherein the control signal comprises atime-varying perturbation signal that provides for the analyte sensor aduty cycle and the variance is determined from a transient response ofthe analyte sensor to the control signal during the duty cycle.
 12. Thedevice of claim 11, storing instructions which cause the processor tomeasure the response signal by determining a work electrode currentsignal.
 13. The device of claim 11, wherein the control signal is asquare-wave signal.
 14. The device of claim 11, wherein the variance isdetermined from the difference in the measured response signal from theanalyte sensor between a beginning and an end of an ‘on’ period of thecontrol signal.
 15. The device of claim 11, storing instructions whichcause the processor to estimate the sensor sensitivity by at leastretrieving a predetermined sensor sensitivity associated with thedetermined variance in the measured response.
 16. The device of claim15, wherein the determined variance comprises a number of analog todigital counts.
 17. The device of claim 11, storing instructions whichcause the processor to determine a validity of the estimated sensorsensitivity.
 18. The device of claim 17, storing instructions whichcause the processor to determine the validity of the estimated sensorsensitivity by at least comparing the estimated sensor sensitivity to apredetermined range.
 19. The device of claim 11, storing instructionswhich cause the processor to determine the calibrated analyte value byat least applying the estimated sensor sensitivity to a signal receivedfrom the analyte sensor.
 20. The device of claim 11, wherein thecalibrated analyte value corresponds to an analyte level in bodily fluidunder a skin surface.